EP0432188B1 - Ameliorations apportees a la sensibilite et a la selectivite de biocapteurs avec membranes a canaux ioniques - Google Patents

Ameliorations apportees a la sensibilite et a la selectivite de biocapteurs avec membranes a canaux ioniques Download PDF

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EP0432188B1
EP0432188B1 EP89909525A EP89909525A EP0432188B1 EP 0432188 B1 EP0432188 B1 EP 0432188B1 EP 89909525 A EP89909525 A EP 89909525A EP 89909525 A EP89909525 A EP 89909525A EP 0432188 B1 EP0432188 B1 EP 0432188B1
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biosensor
membrane
membranes
ion channel
conductance
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EP0432188A1 (fr
EP0432188A4 (en
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Peter Damien John Osman
Bruce Andrew Cornell
Burkhard Raguse
Lionel George King
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Australian Membrane and Biotechnology Research Institute Ltd
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    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001—Enzyme electrodes
    • C12Q1/002—Electrode membranes
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00—Chemistry: molecular biology and microbiology
    • Y10S435/817—Enzyme or microbe electrode
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S436/00—Chemistry: analytical and immunological testing
    • Y10S436/806—Electrical property or magnetic property

Definitions

  • the present invention relates generally to biosensors comprising membranes including at least one ion channel.
  • the conductance of the ion channels is dependent on electric field applied across the membrane.
  • the present invention relates to biosensors comprising discrete arrays of membranes, each membrane including at least one ion channel, and the conductance of each membrane being measurable independently.
  • amphiphilic molecules may be caused to aggregate in solution to form two or three dimensional ordered arrays such as monolayers, micelles, black lipid membranes, and vesicles or liposomes, which vesicles may have a single compartment or may be of the multilamellar type having a plurality of compartments.
  • the selectivity and flux of ions through membranes can depend on the number, size and detailed chemistry of the pores or channels that they possess. It is through these pores or channels that permeating solute molecules pass across the membrane.
  • membranes may incorporate a class of molecules, called ionophores, which facilitate the transport of ions across these membranes.
  • Ion channels are a particular form of ionophore, which as the term implies are channels through which ions may pass through membranes.
  • the measurement of current flow across membranes due to a single ion channel is known and typically yields a current of 4 pA per channel.
  • the present invention seeks to provide biosensors of greater sensitivity.
  • the present invention consists in a biosensor comprising at least one lipid membrane each membrane including at least one gated ion channel, each of said membranes comprising a closely packed array of self-assembling amphiphilic molecules, said at least one gated ion channel having a conductance which is dependent upon an electric field applied across the membrane.
  • the biosensor comprises a plurality of discrete lipid membranes, the conductance of each membrane being measurable independently of the conductance of the other membranes.
  • the present invention consists in a biosensor comprising a plurality of discrete membranes, each membrane including at least one gated ion channel, each of said membranes comprising a closely packed array of self-assembling amphiphilic molecules, the conductance of each of said membranes being measurable independently of the conductance of the other membranes.
  • gated ion channel is defined as an ion channel the passage of ions through which is dependent on the presence of an analyte.
  • field effect ion channel is defined as an ion channel in which the conductance of the ion channel is dependent on an electric field applied across a membrane incorporating the ion channel.
  • amphiphilic molecules are normally surfactant molecules having a hydrophilic "head” portion and one or more hydrophobic "tails".
  • Surfactants may be any of the known types, i.e. cationic (e.g. quaternary ammonium salts), anionic (e.g. organosulfonate salts), zwitterionic (e.g. phosphatidyl cholines, phosphatidyl ethanolamines), membrane spanning lipid, or non-ionic (e.g. polyether materials).
  • the amphiphilic molecules are preferably such that they can be cross-linked.
  • the molecules with a cross-linkable moiety such as vinyl, methacrylate, diacetylene, isocyano or styrene groups either in the head group or in the hydrophobic tail.
  • a cross-linkable moiety such as vinyl, methacrylate, diacetylene, isocyano or styrene groups either in the head group or in the hydrophobic tail.
  • Such groups are preferably connected to the amphiphilic molecule through a spacer group such as described in Fukuda et al. J. Amer. Chem. Soc., 1986, 108 2321-2327.
  • Polymerisation may be performed by any of the known methods for polymerising unsaturated monomers, including heating with or without a free radical initiator, and irradiating with or without a sensitiser or initiator.
  • amphiphilic molecules include or are decorated with at least one moiety cross-linked with at least one corresponding moiety on another of these molecules.
  • the ion channel used in the present invention is preferably selected from the group consisting of peptides capable of forming helices and aggregates thereof, podands, coronands and cryptands. However, it is presently preferred that the ion channel is a peptide capable of forming a helix or aggregates thereof.
  • Peptides which form ⁇ helices generally need to exist as aggregates in the membrane to form ion channels.
  • the ⁇ helical peptides arranged to form aggregates in such a manner that an ion channel is created through the aggregate.
  • the ion channel is a peptide which forms a ⁇ helix.
  • An example of such a peptide is the polypeptide gramicidin A.
  • the ion channel gramicidin A functions as a polar channel which traverses non-polar biological membranes. It is produced either synthetically or extracted from Bacillus brevis . In phospholipid bilayers gramicidin A is thought to exist as a helical dimer which substantially partitions into the hydrophobic region of the bilayer.
  • molecules which may be used as ion channels in the present invention include gramicidin B, gramicidin C, gramicidin D, gramicidin GT, gramicidin GM, gramicidin Gm ⁇ , gramicidin GN ⁇ , gramicidin A' (Dubos), band three protein, bacteriorhodopsin, mellitin, alamethicin, alamethicin analogues, porin, tyrocodine, and tyrothricin.
  • gramicidin when the membrane is a monolayer, a monomer of gramicidin could be used as the ion channel. In a situation where the membrane is a bilayer, a synthetic analogue of dimeric gramicidin A could be used as the ion channel. In addition, where the membrane is a bilayer the ion channel may consist of two gramicidin A monomers, in which each monomer is in a different layer. In this situation the gramicidin A monomers are able to diffuse through the layers and when the two monomers come into alignment an ion channel is formed through the bilayer.
  • the ion channel is gated. This may be done by a receptor moiety attached to, or associated with, an end of the ion channel, the receptor moiety being such that it normally exists in a first state, but when bound to an analyte exists in a second state, said change of state causing a change in the ability of ions to pass through the ion channel.
  • the first state of the receptor moiety will normally be a state in which the passage of ions through the ion channel is prevented or hindered. Attachment of the analyte to the receptor will thus cause the receptor to enter the second state wherein ions may pass through the ion channel.
  • an ion channel may be used to detect as little as a single molecule of analyte the attachment of a single molecule of analyte will cause an ion channel to open and thus cause a leak of ions across the membrane. After a brief time this ion leak may be detected as the signal for the binding of the analyte to the receptor.
  • the alternative arrangement is when the receptor moiety is in the first state ions are able to pass through the ion channel and when in the second state the passage of ions through the ion channel is prevented or hindered.
  • the receptor moiety may be any chemical entity capable of binding to the desired analyte and capable of changing the ion channel from its first state to its second state upon binding to that analyte.
  • the receptor moiety is any compound or composition capable of recognising another molecule. Natural receptors include antibodies, antigens, enzymes, lectins, dyes and the like.
  • the receptor for an antigen is an antibody, while the receptor for an antibody is either an anti-antibody or, preferably, the antigen recognised by that particular antibody.
  • the ion channels of the present invention can be modified by various residues, examples of which are given in Table 1 to achieve the required results.
  • the gated ion channels may be cross-linked with the amphiphilic molecules. However, it is presently preferred that the gated ion channels are able to laterally diffuse through the membrane. As will become clear from the following discussion the ability for the gated ion channels to laterally diffuse through the membrane results in greater sensitivity of the biosensor.
  • the conductance of each membrane is measurable independently of the conductance of the other membranes.
  • the conductance of each membrane is preferably measured by (1) providing a separate high impedance measuring line to each membrane and/or (2) by multiplexing the membranes. It is presently preferred that where a large number of discrete membranes are used that the independent measurements are made by multiplexing the membranes and more preferably by serially multiplexing the membranes.
  • the multiplex lines are preferably low impedance excitation (or signal source) lines (held/clamped) at the excitation value; with a single high impedance current sensing line held at ground reference to complete the circuit for each element of the array when it is switched into circuit. While it is preferred that one current sensing line is used it will be recognised that more than one current sensing line may be provided. Either of these arrangements should result in a biosensor of optimal sensitivity.
  • the gated ion channels are field effect ion channels. It is also preferred that the plurality of discrete membranes including FEICs are arranged in a two dimensional array. It is presently preferred in this arrangement that the multiplex lines are driven from a complex signal such that in the two dimensional array each address line in one dimension has signal components which are cross modulated with the signals from address lines in the other dimension by the field effect ion channel.
  • the biosensor of the present invention comprising a plurality of membranes including field effect ion channels
  • at least one dedicated electrode is provided on one side of each membrane which cooperates with an electrode on the other side of the membrane to enable the application of an electric potential across the membranes. It is preferred that each of these membranes is addressed by multiplexing the signal applied to the respective discrete electrodes.
  • ion channels incorporated in lipid membranes typically consist of a lipid membrane containing an ion channel, which has been modified to change its ionic conductance when an analyte such as an antigen or antibody binds to it.
  • Field effect ion channels FEIC can be used to improve these biosensors and their application involves the following principles:
  • the ratio of "off” to "on” resistance can be increased and shunt capacitance is reduced without increasing the time it takes for a molecule to diffuse to the sensor.
  • field effect ion channels can be used to create a distinctive transduction signal. These techniques can be used to greatly enhance the sensitivity and selectivity of the biosensor.
  • the sensitivity of a biosensor is dependent in part on the ratio of ion channel resistance to lipid membrane resistance, i.e. the "on" to "off” resistance of the ion channel incorporated in the lipid membrane. If the ratio of lipids to ion channels is too large,then the sensor's electrical impedance can be so low that impedance changes due to a sensing event are difficult to detect. Similarly if the absolute number of ion channels is too high then the sensors electrical impedance is lowered, by leakage currents through the ion channels if they are normally blocked, or by the ion channel intrinsic conductance if they are normally open.
  • a reduced surface area implies a longer time for the analyte to diffuse to the point of sensing, and for small concentrations a reduction in probability of detection.
  • the alternative method using flow through techniques, may not be suitable because of the small analyte volumes involved in high sensitivity tests (e.g. one droplet), and because of noise generated by the analyte flow perturbing the membrane.
  • a method proposed here is to set up an array of small area sensors and to switch between them so as to move the point of sensing in the analyte.
  • the switching can be done with a conventional electronic multiplexer, although for two dimensional arrays at least half the address lines would need to have a high impedance.
  • it can be done using FEIC's as part of the sensing ion channel, in which case it is possible to switch between sensing elements in a two dimensional array using low impedance lines and one common high impedance line as described in one of the following examples.
  • Diagnostic reliability can be improved by using a variety of functionally different tests and by measuring the statistics for sets of functionally identical tests. In both of these cases the ability to scan an array of biosensors is useful and both approaches require the availability of a mechanism for switching between biosensors.
  • a second method for improving sensitivity involves the use of FEIC gated ion channel biosensors which are designed with a conductance characteristic which can be readily distinguished from interfering signals such as the lipid membrane conductance and this method will also be discussed in the following examples.
  • Figure 1 shows schematically field modulated ion channels, in which "A” shows modulated head groups; “B” shows modulated side chains; and “C” shows polymeric ion channel.
  • Figure 2 shows a schematic representation of a low impedance biosensor multiplexer.
  • Figure 3 shows a metal or glass electrode in which "A” is a side view and "B” is a view from above.
  • Figure 4 shows a schematic representation of an impedance bridge system.
  • Figure 5 shows a schematic representation of a three terminal bridge.
  • Figure 6 shows a schematic representation of a balanced voltage impedance bridge.
  • Figure 7 shows a schematic representation of a two terminal bridge.
  • Figure 8 shows a biosensor chip.
  • Figure 9 shows a cross-sectional view of the chip of Figure 8 taken along line A-A.
  • Figure 10 shows a cross-sectional view of the chip of Figure 8 taken along line B-B.
  • Polar groups can be incorporated into many parts of an ion channel structure for the purpose of transconductance modulation.
  • ion channels may be employed with polar, dipolar or polarisable residues located: at the head region of the ion channel, on the side chains of the ion channel and at the dimeric junction of an ion channel dimer.
  • the mechanisms for transconductance modulation can be direct modification of the potential profile, distortion of the channel by a conformational change or modification of the potential profile by a conformational change.
  • polar, dipolar or polarisable residues are attached directly or via linker groups to the mouth of the ion channel in the region of the surrounding lipid head groups (Fig. 1a).
  • These ion channels can then be incorporated into either lipid monolayers or bilayers or can be laid down as a secondary film in series connection with a monolayer or bilayer already containing ion channels.
  • This form of ion channel is not as sensitive as those of Examples 3 and 4 because of the surrounding highly polar electrolyte molecules which attenuate field strength in the head group region.
  • the ion channel is held in a lipid bilayer then it is also possible to use opposite polarity polar groups on each side of the bilayer to enhance sensitivity.
  • ion channel is used where monomers (e.g. alamethicin or gramicidin) are combined to form an ion channel.
  • the monomers are chemically or physically linked and contain polar, dipolar or ionised groups as described previously.
  • a field is applied which may assemble, distort or disrupt the ion channel thus modulating its ion conductance.
  • Fig. 1(c) shows a dimer with dipolar residues attached as side chains. Distortion of the dimer by the electric field force acting on the dipolar groups may modulate the dimer transconductance by inducing conformational changes in the region of the dimeric bond.
  • Arrays of field effect ion channels may find application wherever it is desirable to control ion flow.
  • applications may exist in biosensors, or chemical analysis techniques such as electrophoresis.
  • Figure 2 shows schematically a low impedance biosensor multiplexer comprising an array of membranes including gated ion channels 10, an excitation source 12, a modulation source 14, a transfer function analyser 16 an array of address lines 18, and a common sensing line 19.
  • the address lines are on the same side of the channel, and because the signal is well labelled, they can carry low impedance signals without the problems of cross modulation which would exist if they were on opposite sides.
  • the ion channel have a distinctive transconductance characteristic which can be modulated, hence the necessity to use FEIC's.
  • the address electrodes can be AC or DC coupled.
  • a pattern of electrodes and resistors or capacitors is formed by etching a multilayer substrate of alternately electronically conducting and insulating materials. This substrate is then coated with a monolayer or bilayer of lipid.
  • the lipid membrane can be formed directly on some substrate surfaces; alternatively it can be formed on a hydrogel coating over the substrate.
  • the interconnecting resistors and conductors will be insulated from the lipid material while the electrodes are electronically coupled to the membrane either directly or by capacitive coupling.
  • the membrane will be divided into electrically isolated array elements. This may be achieved by making wells over each element of the array.
  • Suitable materials for a substrate may be silicon and its oxides and nitrides, the metals (particularly palladium or platinum), the glasses, ceramics and oxides (particularly aluminium oxide and the titanates and zirconates), the conducting polymers such as nafion, and polypyrrolle, and the insulating polymers used in integrated circuit and capacitor production such as parylene, polyvinylidene fluoride, polyester and polypropylene.
  • Suitable materials for the lipid would be the phospholipids, such as DMPC and DPPC, which are relatively stable. If the lipid is directly coating a metal surface such as palladium, then it would be necessary to substitute a thiol residue such as a sulfhydryl for the phospholipid headgroup.
  • the array In use the array would be placed in a liquid or hydrogel electrolyte containing a common high impedance electrode which is connected to the signal analysis equipment. If very low frequency or DC signals are being used then it may be necessary to use an additional reference electrode to balance the electrochemical potential at the signal electrodes.
  • the signal analysis can use a variety of techniques such as: spectral analysis, cyclic voltammetry, noise analysis, dynamic impedance analysis or statistical analysis. All these methods and preferably carried out in conjunction with the decoding mechanism which is used as described below, to distinguish between interference and true signals and to distinguish between sensing elements.
  • biosensor arrays of biosensors would be useful for multifunctional testing.
  • some forms of biosensor array can also be used to improve sensitivity, selectivity, time response and reliability.
  • a biosensor could be constructed, using for example an array of gated ion channel biosensors made from a field effect ion channel.
  • An appropriate field effect ion channel is given in Example 3.
  • Any of the switching methods described in Example 8 could be used to address the individual elements, although those described for 1 dimensional arrays would be more appropriate for small arrays and those described for 2 dimensional arrays more appropriate for large arrays.
  • the signal analysis methods described in Examples 5 and 8 can be combined to provide an effective addressing and detection algorithm. The reliability of detection could be further enhanced by measuring from many elements for statistical analysis.
  • Ion channels with non linear conductance characteristics with electric field are known to exist.
  • the conductance of a lipid bilayer is known to be much less non linear with electric field than some of these ion channels.
  • Biosensors can be proposed based on the use of modified ion channels in lipid membranes.
  • Lipid membranes are known to present a significant shunt impedance to ion channels thus making it difficult to distinguish ion channel conduction acitivity from lipid conduction.
  • a method for increasing the sensitivity of a biosensor based on ion channels in a lipid membrane may be to use ion channels which have been modified to have an electric field dependent conductance.
  • a complex waveform is applied to the biosensor and compared with those frequency components of the resulting signal which result from the non linear transfer function of the ion channel.
  • An example would be to apply an excitation voltage synthesised from two sine waves to one side of the biosensor membrane and to use a phase lock loop to measure the frequency difference component, in the current passing through the biosensor.
  • V represent the excitation voltage and "A” represents the current passing through the biosensor.
  • f1 and f2 represent the frequencies of the two sine waves in the excitation signal and if they are respectively the n1 and n2 sub-harmonics of a fundamental sinewave "f0" then the detected current signal can be represented as A ⁇ (1/n1-1/n2) x f0 ⁇ .
  • Lipid membranes can have a conductance which varies by a factor of approximately 2 over the usable range of excitation signal whereas an ion channel can be modified to act as a biosensor with a highly non linear conductance which can vary by as much as 50.
  • the ion channel would tend to have a higher level of crossmodulation of the excitation sine waves when compared to the membrane and the improvement in discrimination would be:
  • a n1-n2 x f0 ion channel A n1-n2 x f0 membrane
  • the difference frequency of the above example should be greater than the Nyquist frequency for the shortest pulse period considered significant in the analysis.
  • modalities for discriminating ion channel from lipid membrane conductance are: optical and/or acoustic excitation of the ion channel.
  • cell areas of from 0.1 to 100 micron are typical.
  • the limiting sensitivity is defined as the conductance of a single channel divided by total conductance of the sensor then the dependence of limiting sensitivity on area of such a system can be expressed in terms of functions of: the area of the ion channel "f1(Ai)", the membrane area "f2(Am)” and the area of ion leakage at the membrane perimeter f3(Ae) as: 1 / ( 1 + f2(Am)/f1(Ai) + f3(Ae)/f1(Ai) )
  • f1 and f2 are, to a first approximation, linear, giving admittance per unit area.
  • f3 is a more indeterminate function giving leakage admittance around the biosensor cell perimeter. In a circular cell it is approximately proportional to (Rm-Re) where Rm is the radius of the biosensor and Re is the radius to the region where edge leakage occurs.
  • a biosensor detects by binding analyte molecules of cross sectional area "Aan" to a few ion channels which are consequently opened or closed, then if there are N1 ion channels which can laterally diffuse through the membrane then the limiting sensitivity is given as:- Am Aan x 1 1 + N1 + f2(Am)/f1(Ai) + f3(Ae)/fi(Ai)
  • the sensitivity limit is given as: 1 Aan x N1 1 + N1 + f2(Am)/f1(Ai) + f3(Ae)/fi(Ai)
  • the electrical sensitivity can be greatly increased by reducing the limiting effect of membrane area on electrical sensitivity, and by retaining the information contained in single ion activity while allowing more ion channels to be used.
  • the increased number of ion channels will also increase time response by reducing the lateral diffusion times.
  • Improved sensitivity and time response in a biosensor, based on an ion channel in a lipid membrane can be achieved by independently sensing a number of small cells distributed over the active surface area, by multiplexing or by parallel amplification or both.
  • Biosensors based on field effect ion channels which have been modified may also be multiplexed.
  • the speed of response and sensitivity of the biosensor described above are optimal when a system of parallel amplifiers is used on an array of close packed cells.
  • a serially multiplexed system with close packed cells will be equally sensitive as the parallel system but will have a longer time response which improves with the number of parallel signal paths in the network. Spacing the sensing elements and multiplexing between them will result in an improvement in response time but a loss of sensitivity proportional to the ratio of the sensor area/sensing area.
  • biosensors described below typically use a 2 or 3 terminal bridge connected to a gated ion channel modified in the membrane.
  • multiplexing is carried out entirely by excitation electrodes with the high impedance sensing electrode(s) not being associated directly with the multiplexor.
  • This example describes a device for enhancing sensitivity in a biosensor based on a gated ion channel in a lipid bilayer.
  • FIG. 3 shows schematically metal on glass electrodes 20 from the side (a) and from above (b).
  • the metal on glass electrodes 20 consists of a glass substrate 22, active electrodes 24, connector pads 26 and electrical connections 28 connecting connector pads 26 with electrodes 24.
  • the electrical connections 28 and active electrodes 24 are sputtered layers.
  • Connector pads 26 are electroplated as per figure 3 and the electrode 20 is then cleaned with distilled deionised water and by ethanol vapour degreasing or in a soxhlet extractor.
  • This form of biosensor uses a combination of bound alcohol and lipid as an insulator.
  • the shadow mask creates a penumbral region of electrically discontinuous metal around the perimeter of the metallisation, which serves to anchor lipid support material and allow a well insulating membrane to surround and cover the electrically continuous region. Shadow masking is preferred because it avoids the chemical contamination associated with photolithography. If photolithography is used then the cleaning process described above should be repeated after the normal post photolithography cleaning procedures have been followed.
  • FIG. 5 shows a standard voltage clamp amplifier
  • Fig. 6 shows a balanced voltage bridge for measuring differential impedance with a biosensor containing two active electrodes. Both elements are coated in lipid but only one includes the biosensing gated ion channels.
  • Figure 4 shows an example of a method to measure ion channel impedance in a membrane by using the non-linear conductance property of the ion channel.
  • Figure 4 shows a local oscillator 31 which might typically run at 10kHz.
  • Frequency dividers 32 and 33 derive signals of frequency F/n1 and F/n2 from the local oscillator 31.
  • a summing amplifier 34 adds the two signals from frequency dividers 32 and 33, whilst buffer amplifiers 35 and 36 supply a signal to the sensing electrode.
  • Buffer amplifier 36 also inverts the signal so that it is the opposite polarity to the signal from buffer amplifier 35, however, this inverted signal is only required where the preamplifier used is as shown in Figure 6.
  • the system for switching (multiplexing) the signal to an array of electrodes and sensing the resultant signal with a single current sensing amplifier is shown generally as 37 and described in more detail in Figures 5, 6 and 7.
  • the sensed signal is then further amplified by an amplifier 38 and the component of the signal with a frequency of (F/n1 - F/n2) is detected and amplified by a phase lock loop detector 39. Because this signal component results from the non-linear conductance of the ion channel it can be used to preferentially distinguish changes in the ion channel conductance from the rest of the membrane impedance which has a relatively linear conductance.
  • Figures 5, 6 and 7 show forms of preamplifiers suitable for use with the sensors described in the examples.
  • Figure 5 shows a preamplifier which is more suitable for single sensors; while Figures 6 and 7 show preamplifiers which are more readily used with an array of sensors.
  • the preamplifier shown in Figure 5 is a standard three terminal impedance bridge comprising an amplifier 41 which supplies enough current to counter electrode 42 so that a reference electrode 43 is always held at the same potential as the command voltage.
  • the reference electrode 43 is connected to a high impedance negative feedback input of amplifier 41 so that it accurately monitors the potential of the electrolyte solution and controls the current to the counter electrode so that the electrolyte solution is clamped to the same potential as the command voltage.
  • the active electrode 44 is coated with the membrane and held at a zero value of potential so that current must flow into it from the counter electrode 42 dependent on the impedance of the membrane.
  • the amplifier 45 measures this current by forcing it through a resistor 46.
  • the conductance of the membrane coating the active electrode 44 can be determined from the measured value of the potential of the electrolyte and the current passing through the membrane.
  • the preamplifier and electrode arrangement shown in Figure 6 comprises a balanced bridge consisting of an electrode 51 which is coated with the lipid membrane containing gated ion channels and an electrode 52 which is coated with a lipid membrane only.
  • the two electrodes are supplied with signals which are identical but opposite in polarity so that if the electrode conductances are equal there is a zero potential in the electrolyte in which they are both immersed.
  • a sensor electrode 53 measures imbalances in the potential of the electrolyte so that if the conductance of the electrode 51 was altered by a biosensor reaction (i.e. opening or closing of the gated ion channel) then the change in potential would be sensed by electrode 53 and amplified by a high impedance amplifier 54.
  • Electrodes 51 and 52 can be a pair in an array of such pairs which can be addressed by switching the excitation signal to them.
  • the preamplifier shown in Figure 7 represents a two terminal impedance bridge in which an amplifier 56 supplies an excitation signal to an electrode 57 which is coated with a membrane. Electrode 57 is one of an array of electrodes and the excitation signal can be switched to each electrode in the array. An electrode 58 detects the current passing through electrode 57 and amplifies it with a high impedance amplifier 59. Thus the conductance of an array of electrodes such as 57 can be measured.
  • the biosensor is fabricated using a combination of silicon integrated circuit technology and lipid coating methods.
  • Figures 8 - 10 shows details of four mask levels necessary for fabrication with Figures 9 and 10 showing cross-sectional views taken along line A-A and B-B of Figure 8 respectively.
  • the chip size is 7mm x 5mm with the four mask levels required to pattern the layers given as Polysilicon, silicon dioxide, Aluminium and Nitride. These are shown as Polysilicon 60, silicon dioxide 62, Aluminium 64 and Nitride 66, electrode metallisation (gold, palladium or platinum) 67.
  • the significance of these levels is as follows:-
  • a layer of deposited silicon nitride is the primary electrical insulation layer and covers the whole surface of the chip with the exception of windows over the pair of sensing electrodes 70 and bonding pads 72. Wire connecting leads 74 are provided to the bonding pads 72.
  • an electrode well 78 where the biosensor membrane is positioned is provided in each one of the each pair of electrodes 70.
  • the starting material is a 6 inch diameter wafer of 100 single crystal silicon.
  • the pattern shown is arranged as a general test unit which shows how electrodes can be either close packed or separated and how they can be used in various bridge configurations.
  • the two close packed elements are used to provide a cross check on each other.
  • the 10 pairs can then be used as individual biosensing elements to scan a surface of analyte using preamplifiers such as those given in figures 6 and 7.
  • Another arrangement is to use them in a number of bridge circuits grouped so that some contain biosensitive ion channels, some contain ion channels which have not been modified for biosensitivity and the remainder contain only lipid material.
  • Such grouped elements can be measured separately and compared after amplification; alternatively differential measurements can be carried out using bridges as per figures 6.
  • the multiplexor circuitry requires that the active elements be attached to low impedance circuitry so that conventional three terminal bridges are not appropriate. It is also desirable for cost effectiveness that the high impedance element should not be located on the sensor chip. Arrangements which achieve this are given in figure 4 and use the amplifiers outlined in Figures 6 and 7.

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Claims (22)

  1. Biocapteur comprenant au moins une membrane lipidique, chaque membrane contenant au moins un canal ionique déclenché, chacune desdites membranes comprenant un agencement très tassé de molécules amphiphiles s'auto-assemblant, au moins une électrode spécialisée prévue sur une face de la membrane qui coopère avec une électrode sur l'autre face de la membrane pour permettre l'application d'un potentiel électrique à travers la membrane, le au moins un canal ionique déclenché ayant une conductance qui dépend du potentiel électrique appliqué à travers la membrane.
  2. Biocapteur selon la revendication 1, où le canal ionique est modifié par incorporation ou élimination de groupes polaires, dipolaires ou polarisables.
  3. Biocapteur selon la revendication 1 ou la revendication 2, où le biocapteur comprend un certain nombre de membranes distinctes, la conductance de chaque membrane étant mesurable indépendamment de la conductance des autres membranes.
  4. Biocapteur selon la revendication 3, où au moins une électrode spécialisée est prévue sur une face de chaque membrane qui coopère avec une électrode sur l'autre face de chaque membrane pour permettre l'application d'un potentiel électrique à travers la membrane, les membranes étant multiplexées en multiplexant le signal appliqué aux ou mesuré des électrodes distinctes respectives.
  5. Biocapteur comprenant un certain nombre de membranes distinctes, chaque membrane comprenant au moins un canal ionique déclenché, chacune desdites membranes comprenant un agencement très serré de molécules amphiphiles s'auto-assemblant, la conductance de chacune desdites membranes étant mesurable indépendamment de la conductance des autres membranes, au moins une électrode spécialisée prévue sur une face de chaque membrane qui coopère avec une électrode sur l'autre face de chaque membrane, pour permettre l'application d'un potentiel électrique à travers la membrane, les membranes étant multiplexées en multiplexant le signal appliqué à ou mesuré des électrodes distinctes respectives.
  6. Biocapteur selon l'une quelconque des revendications 1 à 5, où le canal ionique est sélectionné dans le groupe consistant en peptides capables de former des hélices et leurs agrégats, podands, coronands et cryptands.
  7. Biocapteur selon la revendication 6, où le canal ionique est un peptide capable de former une hélice ou ses agrégats.
  8. Biocapteur selon la revendication 7, où le canal ionique est un peptide qui forme une hélice β.
  9. Biocapteur selon la revendication 8, où le canal ionique est la gramicidine ou ses analogues.
  10. Biocapteur selon la revendication 9, où le canal ionique est la gramicidine A ou ses analogues.
  11. Biocapteur selon l'une quelconque des revendications 1 à 10, où le canal ionique déclenché peut diffuser latéralement dans la membrane lipidique.
  12. Biocapteur selon l'une quelconque des revendications 1 à 11, où chaque membrane lipidique est pourvue d'une ligne d'adresse séparée à haute impédance, et/ou où les membranes sont multiplexées, pour ainsi permettre de mesurer la conductance de chaque membrane lipidique.
  13. Biocapteur selon la revendication 12, où les membranes sont multiplexées, permettant ainsi de mesurer la conductance de chaque membrane lipidique.
  14. Biocapteur selon la revendication 13, où les membranes sont multiplexées en série.
  15. Biocapteur selon la revendication 13 ou la revendication 14, où les membranes sont connectées à des lignes multiplexes de faible impédance, et où au moins une ligne de captage de courant est prévue, pour ainsi permettre de mesurer la conductance de chaque membrane lipidique.
  16. Biocapteur selon la revendication 15, où il y a une ligne captant le courant.
  17. Biocapteur selon l'une quelconque des revendications 1 à 11, qui est pourvu soit d'un seul capteur de courant qui mesure le signal de chacune d'un certain nombre de lignes d'adresse à faible impédance, en commutant entre elles,ou bien d'un certain nombre de capteurs de courant, électriquement isolés les uns des autres, dont chacun mesure les signaux d'un groupe de lignes d'adresse.
  18. Biocapteur selon l'une quelconque des revendications 1 à 11, qui est pourvu soit d'un seul capteur de courant qui mesure le signal de chacune d'un certain nombre de lignes d'adresse à haute impédance, en commutant entre elles, ou bien d'un certain nombre de capteurs de courant électriquement isolés les uns des autres, dont chacun mesure les signaux d'un groupe de lignes d'adresse.
  19. Biocapteur selon l'une quelconque des revendications 12 à 18, où les canaux ioniques déclenchés sont des canaux ioniques à effet de champ.
  20. Biocapteur selon la revendication 19, où les membranes distinctes sont agencées en un agencement bidimensionnel.
  21. Biocapteur selon la revendication 20, où les lignes multiplex sont attaquées par un signal complexe, de manière que dans l'agencement bidimensionnel, chaque ligne d'adresse dans une dimension des composantes du signal qui sont modulées avec les signaux des lignes d'adresse dans l'autre dimension par le canal ionique à effet de champ.
  22. Biocapteur selon l'une quelconque des revendications 1 à 11, où chaque membrane lipidique est pourvue d'une ligne d'adresse de haute impédance, et qui est pourvue soit d'un amplificateur séparé pour chaque membrane ou d'un seul amplificateur qui peut être commuté entre chaque membrane ou d'un certain nombre d'amplificateurs qui peuvent être commutés entre les membranes, pour ainsi permettre de mesurer la conductance de chaque membrane.
EP89909525A 1988-08-18 1989-08-17 Ameliorations apportees a la sensibilite et a la selectivite de biocapteurs avec membranes a canaux ioniques Expired - Lifetime EP0432188B1 (fr)

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Families Citing this family (125)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5328847A (en) * 1990-02-20 1994-07-12 Case George D Thin membrane sensor with biochemical switch
DK0639269T3 (da) * 1991-03-27 2002-10-07 Ambri Ltd Ionreservoir ved elektrodeoverflade
US6051380A (en) * 1993-11-01 2000-04-18 Nanogen, Inc. Methods and procedures for molecular biological analysis and diagnostics
US5605662A (en) 1993-11-01 1997-02-25 Nanogen, Inc. Active programmable electronic devices for molecular biological analysis and diagnostics
US5632957A (en) * 1993-11-01 1997-05-27 Nanogen Molecular biological diagnostic systems including electrodes
US6048690A (en) * 1991-11-07 2000-04-11 Nanogen, Inc. Methods for electronic fluorescent perturbation for analysis and electronic perturbation catalysis for synthesis
US6569382B1 (en) * 1991-11-07 2003-05-27 Nanogen, Inc. Methods apparatus for the electronic, homogeneous assembly and fabrication of devices
US6017696A (en) * 1993-11-01 2000-01-25 Nanogen, Inc. Methods for electronic stringency control for molecular biological analysis and diagnostics
US6652808B1 (en) * 1991-11-07 2003-11-25 Nanotronics, Inc. Methods for the electronic assembly and fabrication of devices
US5849486A (en) 1993-11-01 1998-12-15 Nanogen, Inc. Methods for hybridization analysis utilizing electrically controlled hybridization
US5846708A (en) * 1991-11-19 1998-12-08 Massachusetts Institiute Of Technology Optical and electrical methods and apparatus for molecule detection
IL103674A0 (en) * 1991-11-19 1993-04-04 Houston Advanced Res Center Method and apparatus for molecule detection
ATE143730T1 (de) * 1992-04-22 1996-10-15 Ecole Polytech Lipidmembranen fur biosensoranwendungen
WO1994007593A1 (fr) * 1992-10-01 1994-04-14 Australian Membrane And Biotechnology Research Institute Membranes de capteur ameliorees
JP3316816B2 (ja) * 1992-12-03 2002-08-19 オーストラリアン メンブレイン アンド バイオテクノロジィ リサーチ インスティチュート イオンチャンネル通門の競合阻害によるアナライト検出
US5401377A (en) * 1993-08-06 1995-03-28 Biomedix, Inc. Ion-selective sensor with polymeric membrane having phospholipid dispersed therein
US5494831A (en) * 1993-08-30 1996-02-27 Hughes Aircraft Company Electrochemical immunosensor system and methods
WO1995008637A1 (fr) * 1993-09-21 1995-03-30 Washington State University Research Foundation Dosage immunologique comportant un recepteur de canal d'ions conjugue a un ligand immobilise dans un film de lipides
US6319472B1 (en) 1993-11-01 2001-11-20 Nanogen, Inc. System including functionally separated regions in electrophoretic system
US20040077074A1 (en) * 1993-11-01 2004-04-22 Nanogen, Inc. Multi-chambered analysis device
US6309602B1 (en) 1993-11-01 2001-10-30 Nanogen, Inc. Stacked, reconfigurable system for electrophoretic transport of charged materials
US6225059B1 (en) 1993-11-01 2001-05-01 Nanogen, Inc. Advanced active electronic devices including collection electrodes for molecular biological analysis and diagnostics
US6638482B1 (en) 1993-11-01 2003-10-28 Nanogen, Inc. Reconfigurable detection and analysis apparatus and method
US6287517B1 (en) 1993-11-01 2001-09-11 Nanogen, Inc. Laminated assembly for active bioelectronic devices
US6375899B1 (en) 1993-11-01 2002-04-23 Nanogen, Inc. Electrophoretic buss for transport of charged materials in a multi-chamber system
US6254827B1 (en) 1993-11-01 2001-07-03 Nanogen, Inc. Methods for fabricating multi-component devices for molecular biological analysis and diagnostics
US7582421B2 (en) * 1993-11-01 2009-09-01 Nanogen, Inc. Methods for determination of single nucleic acid polymorphisms using a bioelectronic microchip
US7172864B1 (en) 1993-11-01 2007-02-06 Nanogen Methods for electronically-controlled enzymatic reactions
US6315953B1 (en) * 1993-11-01 2001-11-13 Nanogen, Inc. Devices for molecular biological analysis and diagnostics including waveguides
US7101661B1 (en) 1993-11-01 2006-09-05 Nanogen, Inc. Apparatus for active programmable matrix devices
US6726880B1 (en) 1993-11-01 2004-04-27 Nanogen, Inc. Electronic device for performing active biological operations and method of using same
US7314708B1 (en) 1998-08-04 2008-01-01 Nanogen, Inc. Method and apparatus for electronic synthesis of molecular structures
US6331274B1 (en) 1993-11-01 2001-12-18 Nanogen, Inc. Advanced active circuits and devices for molecular biological analysis and diagnostics
US6068818A (en) 1993-11-01 2000-05-30 Nanogen, Inc. Multicomponent devices for molecular biological analysis and diagnostics
AU777515B2 (en) * 1993-11-01 2004-10-21 Nanogen, Inc. Devices and systems for molecular biological reactions, analysis and diagnostics
US5556528A (en) * 1994-05-10 1996-09-17 Biotechnology Research & Development Corporation Structures with field responsive permeation control
US6379897B1 (en) * 2000-11-09 2002-04-30 Nanogen, Inc. Methods for gene expression monitoring on electronic microarrays
US6403367B1 (en) * 1994-07-07 2002-06-11 Nanogen, Inc. Integrated portable biological detection system
US7857957B2 (en) 1994-07-07 2010-12-28 Gamida For Life B.V. Integrated portable biological detection system
AT402935B (de) * 1994-10-19 1997-09-25 Pittner Fritz Biorekognitions-gesteuerter, ionenfluss-modulirender biosensor
AUPM950094A0 (en) 1994-11-16 1994-12-08 Australian Membrane And Biotechnology Research Institute Detection device and method
US20120160687A1 (en) 1995-03-17 2012-06-28 President And Fellows Of Harvard College Characterization of individual polymer molecules based on monomer-interface interactions
US6362002B1 (en) * 1995-03-17 2002-03-26 President And Fellows Of Harvard College Characterization of individual polymer molecules based on monomer-interface interactions
AUPN366995A0 (en) * 1995-06-20 1995-07-13 Australian Membrane And Biotechnology Research Institute Self-assembly of bilayer membrane sensors
US5879878A (en) * 1995-06-20 1999-03-09 Australian Membrane And Biotechnology Research Institute Method of producing a first layer electrode membrane for a biosensor
US5719033A (en) * 1995-06-28 1998-02-17 Motorola, Inc. Thin film transistor bio/chemical sensor
US20040086917A1 (en) * 1995-09-27 2004-05-06 Nanogen, Inc. Methods for electronic fluorescent perturbation for analysis and electronic perturbation catalysis for synthesis
WO1997020203A1 (fr) * 1995-11-28 1997-06-05 Thomas Schalkhammer Nouvelles membranes et nouveaux capteurs d'adn/arn a membrane
US6348319B1 (en) * 1996-02-08 2002-02-19 Australian Membrane And Biotechnology Research Institute Enzyme detection biosensors
AUPN980796A0 (en) 1996-05-13 1996-06-06 Australian Membrane And Biotechnology Research Institute Improved reservoir components
US5756879A (en) * 1996-07-25 1998-05-26 Hughes Electronics Volatile organic compound sensors
US6503452B1 (en) 1996-11-29 2003-01-07 The Board Of Trustees Of The Leland Stanford Junior University Biosensor arrays and methods
EP0941474B1 (fr) * 1996-11-29 2006-03-29 The Board Of Trustees Of The Leland Stanford Junior University Agencements de membranes a bicouches fluidiques supportees, adressables independamment, et procedes d'utilisation correspondants
US6699719B2 (en) * 1996-11-29 2004-03-02 Proteomic Systems, Inc. Biosensor arrays and methods
US6706473B1 (en) 1996-12-06 2004-03-16 Nanogen, Inc. Systems and devices for photoelectrophoretic transport and hybridization of oligonucleotides
US5945774A (en) * 1997-03-28 1999-08-31 Industrial Technology Research Institute Open package for crystal oscillator chips
WO1998055855A1 (fr) * 1997-06-04 1998-12-10 Australian Membrane And Biotechnology Research Institute Biocapteur perfectionne impliquant l'utilisation de parties a sensibilite optique
CA2298540A1 (fr) 1997-08-20 1999-02-25 David J. Julius Sequences nucleotidiques codant pour le recepteur de la capsicine, polypeptides lies au recepteur de la capsicine et leur utilisation
DE19741715A1 (de) * 1997-09-22 1999-03-25 Hoechst Ag Pentopyranosyl-Nucleosid, seine Herstellung und Verwendung
US20020144905A1 (en) 1997-12-17 2002-10-10 Christian Schmidt Sample positioning and analysis system
US7244349B2 (en) * 1997-12-17 2007-07-17 Molecular Devices Corporation Multiaperture sample positioning and analysis system
ES2163284T3 (es) 1997-12-17 2002-01-16 Ecole Polytech Posicionamiento y caracterizacion electrofisiologica de celulas individuales y sistemas de membranas reconstituidos sobre soportes microestructurados.
EP0991938B1 (fr) * 1998-02-02 2004-06-30 MDS Sciex Procede et appareil de detection d'evenements de liaison moleculaire
US5961934A (en) * 1998-02-18 1999-10-05 Biospace International Inc. Dynamically controlled crystallization method and apparatus and crystals obtained thereby
DK173381B1 (da) * 1998-03-03 2000-09-11 Unisense Aps Fremgangsmåde til at regulere følsomheden af en mikrosensor samt mikrosensor, der gør brug af fremgangsmåden
GB9812783D0 (en) 1998-06-12 1998-08-12 Cenes Ltd High throuoghput screen
EP1125120A1 (fr) * 1998-10-27 2001-08-22 President And Fellows of Harvard College Canaux ioniques biologiques dans des detecteurs nanofabriques
US6267872B1 (en) * 1998-11-06 2001-07-31 The Regents Of The University Of California Miniature support for thin films containing single channels or nanopores and methods for using same
ATE513209T1 (de) 1998-12-05 2011-07-15 Xention Ltd Grenzflächen-patch-clamp-verfahren und -gerät
US7270969B2 (en) 1999-05-05 2007-09-18 Phylogica Limited Methods of constructing and screening diverse expression libraries
WO2001034764A2 (fr) * 1999-11-08 2001-05-17 Cytion S.A. Appareil et procedes de positionnement et d'analyse d'objets membranaires biologiques
US6916665B2 (en) * 2000-02-11 2005-07-12 The Texas A&M University System Biosensor compositions and methods of use
US20030139336A1 (en) * 2000-03-21 2003-07-24 Norwood James Henry Interface patch clamping
EP1287351A2 (fr) * 2000-05-18 2003-03-05 The Board Of Trustees Of The Leland Stanford Junior University Procedes et dispositifs relatifs a des reseaux de bicouches lipidiques
US20030129581A1 (en) * 2000-06-06 2003-07-10 Owen David Geraint Patch-clamping method and apparatus
US7270730B2 (en) 2000-08-04 2007-09-18 Essen Instruments, Inc. High-throughput electrophysiological measurement system
US7067046B2 (en) * 2000-08-04 2006-06-27 Essen Instruments, Inc. System for rapid chemical activation in high-throughput electrophysiological measurements
US7008524B2 (en) * 2000-10-03 2006-03-07 Hrl Laboratories, Llc Sensors with variable response behavior
US6730212B1 (en) 2000-10-03 2004-05-04 Hrl Laboratories, Llc Sensor for chemical and biological materials
SE0004334D0 (sv) * 2000-11-24 2000-11-24 Sahltech Ab Electron spectroscopy
US6835552B2 (en) * 2000-12-14 2004-12-28 The Regents Of The University Of California Impedance measurements for detecting pathogens attached to antibodies
DE60213948T2 (de) * 2001-01-18 2007-03-08 Newcastle University Ventures Ltd. Biosensor mit kovalent gebundenen membranüberspannenden proteinen
US20030104428A1 (en) * 2001-06-21 2003-06-05 President And Fellows Of Harvard College Method for characterization of nucleic acid molecules
EP1278064B1 (fr) * 2001-07-18 2008-07-02 CSEM Centre Suisse d'Electronique et de Microtechnique SA Agencement de micro-électrodes à haute densité
US6783645B2 (en) * 2001-12-18 2004-08-31 Dionex Corporation Disposable working electrode for an electrochemical cell
JP2005526972A (ja) * 2002-05-02 2005-09-08 シファーゲン バイオシステムズ， インコーポレイテッド 多糖系ヒドロゲルをコーティングした表面を有するバイオチップ
WO2003095669A1 (fr) * 2002-05-10 2003-11-20 The Texas A & M University System Detection stochastique par interactions covalentes
US7601493B2 (en) * 2002-07-26 2009-10-13 Nanogen, Inc. Methods and apparatus for screening and detecting multiple genetic mutations
US7267751B2 (en) * 2002-08-20 2007-09-11 Nanogen, Inc. Programmable multiplexed active biologic array
US20040110205A1 (en) * 2002-09-23 2004-06-10 Hui Wang Methods and systems for nanopore data analysis
US20040121377A1 (en) * 2002-10-05 2004-06-24 Chiaki Ishii Spatially encoded and mobile arrays of tethered lipids
US20040092004A1 (en) * 2002-11-07 2004-05-13 Hrl Laboratories, Llc Sensor for detection of enzyme and enzyme detection method for aerosolized bacteria in the enviromnment
US20040197821A1 (en) * 2003-04-04 2004-10-07 Bauer Alan Joseph Rapid-detection biosensor
US8187865B2 (en) * 2003-06-12 2012-05-29 California Institute Of Technology Nanowire sensor, sensor array, and method for making the same
WO2005017025A2 (fr) * 2003-08-15 2005-02-24 The President And Fellows Of Harvard College Etude de molecules de polymere et conformations avec un nanopore
US7829185B2 (en) * 2003-08-26 2010-11-09 University Of Cincinnati Selectively permeable film supported membrane
KR100613398B1 (ko) * 2003-11-25 2006-08-17 한국과학기술연구원 캔틸레버 센서형 분석 시스템, 제조 방법 및 이를 이용한극미세 물질 감지 방법
US7238485B2 (en) 2004-03-23 2007-07-03 President And Fellows Of Harvard College Methods and apparatus for characterizing polynucleotides
US7828954B2 (en) * 2004-09-21 2010-11-09 Gamida For Life B.V. Electrode based patterning of thin film self-assembled nanoparticles
US7314542B2 (en) * 2004-09-23 2008-01-01 Nanogen, Inc. Methods and materials for optimization of electronic transportation and hybridization reactions
JP2008517268A (ja) * 2004-10-14 2008-05-22 エレクトロニック・バイオサイエンシーズ・エルエルシー 検体の生体指紋を生成するための集積化感知アレイ
US7741106B2 (en) * 2005-09-21 2010-06-22 Moyle William R Sensors for biomolecular detection and cell classification
JP5220623B2 (ja) * 2006-03-16 2013-06-26 ユニバーサル ナノセンサー テクノロジーズ インコーポレーテッド 誘電率検出方法及びシステム
US20070224637A1 (en) * 2006-03-24 2007-09-27 Mcauliffe Joseph C Oxidative protection of lipid layer biosensors
EP2122344B8 (fr) 2007-02-20 2019-08-21 Oxford Nanopore Technologies Limited Système de capteur bicouche lipidique
DE102007043132B4 (de) * 2007-09-11 2012-07-26 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Biosensor und Verfahren zum Messen einer Konzentration eines Analyten in einem Medium
GB0724736D0 (en) 2007-12-19 2008-01-30 Oxford Nanolabs Ltd Formation of layers of amphiphilic molecules
WO2010004115A1 (fr) * 2008-06-27 2010-01-14 Stmicroelectronics (Research & Development) Limited Dispositif d'analyse biologique de type pixel, biocapteur cmos et procedes de fabrication correspondants
EP2580588B1 (fr) 2010-06-08 2014-09-24 President and Fellows of Harvard College Dispositif à nanopores avec membrane lipidique artificielle sur support de graphène
US11346798B2 (en) 2010-07-12 2022-05-31 Arizona Board Of Regents On Behalf Of Arizona State University Methods and device for tuning multiplexed markers for disease assay
GB201202519D0 (en) 2012-02-13 2012-03-28 Oxford Nanopore Tech Ltd Apparatus for supporting an array of layers of amphiphilic molecules and method of forming an array of layers of amphiphilic molecules
EP4235174A3 (fr) 2012-04-09 2024-01-24 Takulapalli, Bharath Transistor à effet de champ, dispositif doté du transistor et procédé pour le former et l'utiliser
US8895249B2 (en) 2012-06-15 2014-11-25 Illumina, Inc. Kinetic exclusion amplification of nucleic acid libraries
GB201313121D0 (en) 2013-07-23 2013-09-04 Oxford Nanopore Tech Ltd Array of volumes of polar medium
EP2973456A4 (fr) * 2013-03-15 2016-11-16 Bharath Takulapalli Réseau de capteurs de biomarqueur et circuit, et leurs procédés d'utilisation et de formation
DE102013013295A1 (de) 2013-08-12 2015-02-12 Airbus Defence and Space GmbH Ionendosiervorrichtung für eine Energiespeichervorrichtung, Verfahren zum Herstellen einer Ionendosiervorrichtung und Energiespeichervorrichtung
CN106796223A (zh) 2014-08-13 2017-05-31 亚利桑那州立大学董事会 非侵入式体液压力感测
GB201418512D0 (en) 2014-10-17 2014-12-03 Oxford Nanopore Tech Ltd Electrical device with detachable components
WO2017184790A1 (fr) 2016-04-19 2017-10-26 Takulapalli Bharath Capteur de nanopores, structure et dispositif comprenant le capteur, et procédés de formation et d'utilisation correspondants
GB201611770D0 (en) 2016-07-06 2016-08-17 Oxford Nanopore Tech Microfluidic device
US11073508B2 (en) 2017-03-28 2021-07-27 Arizona Board Of Regents On Behalf Of The University Of Arizona Rapid conductance based ion channel analysis
EP3648668B1 (fr) * 2017-07-03 2023-10-04 Roche Diabetes Care GmbH Procédé, unité électronique et système de détection de propriétés in vivo d'un biocapteur
GB2568895B (en) 2017-11-29 2021-10-27 Oxford Nanopore Tech Ltd Microfluidic device
US11789006B2 (en) 2019-03-12 2023-10-17 Oxford Nanopore Technologies Plc Nanopore sensing device, components and method of operation
KR102322684B1 (ko) * 2019-07-18 2021-11-04 성균관대학교산학협력단 바이오 센서, 이의 제조 방법 및 이를 이용한 이온 검출 방법

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS59212757A (ja) * 1983-05-19 1984-12-01 Toshiba Corp 流通型イオンセンサ体
EP0138150A3 (fr) * 1983-10-05 1988-06-01 E.I. Du Pont De Nemours And Company Membranes pour électrodes de diagnostic à paires spécifiques d'enzyme/ionophore
CA1223039A (fr) * 1984-03-26 1987-06-16 Michael Thompson Detecteurs selectifs d'agents chimiques avec membranes a modulation d'admittance
US4661235A (en) * 1984-08-03 1987-04-28 Krull Ulrich J Chemo-receptive lipid based membrane transducers
US4776944A (en) * 1986-03-20 1988-10-11 Jiri Janata Chemical selective sensors utilizing admittance modulated membranes
GB8622788D0 (en) * 1986-09-22 1986-10-29 Atomic Energy Authority Uk Sensor

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ATE136119T1 (de) 1996-04-15
DE68926118D1 (de) 1996-05-02
US5234566A (en) 1993-08-10
WO1990002327A1 (fr) 1990-03-08
EP0432188A1 (fr) 1991-06-19
EP0432188A4 (en) 1991-10-16
DE68926118T2 (de) 1996-08-22
CA1315338C (fr) 1993-03-30

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